Electric field generation system and use method

Abstract

The invention discloses an electric field generating system and a using method, the electric field generating system comprises a collecting electrode and an electric field generating electrode, the collecting electrode is used for being implanted into a central area and / or a peripheral area of target tissue to collect electric signals of the target tissue and / or surrounding tissue; the electric field generating electrode is used for being implanted into the central area and / or the peripheral area of the target tissue so as to generate a target electric field to the target tissue. By arranging the implantable collecting electrode and the implantable electric field generating electrode, the portable electric field collecting device can be conveniently carried by a living body, stimulation to the body surface of the living body and the like can be avoided, and the functions of collecting electric signals and generating a target electric field can be achieved at the same time.

Description

Technical Field

[0001] The present disclosure generally relates to the field of medical technology. More specifically, the present disclosure relates to an electric field generating system and method of use. Background Art

[0002] Unlimited proliferation and division of cancer cells is a key factor in the development of cancer. Current cancer treatment methods have certain limitations, and we need to explore new, more effective and highly specific means to interfere with cancer cell division. Tumor Therapy Fields is a new anti-tumor therapy that uses low-intensity, medium-frequency alternating electric fields to act on the microtubules of proliferating cancer cells, interfere with tumor cell mitosis, cause apoptosis of affected cancer cells and inhibit tumor growth.

[0003] The electric field therapy devices currently used for tumor treatment are usually non-invasive, and they achieve the purpose of inhibiting tumor growth by attaching patch electrodes to the surface of the body and generating an electric field. However, this non-invasive device is bulky, large, and inconvenient to carry. In particular, for treatment scenarios where the electric field needs to act on the head, the patient needs to keep a bald head so that the patch electrodes can be attached to the scalp. This is not only not conducive to the patient's image, but the long-term attachment of the electrodes and the generation of electric fields will also irritate the scalp, which may cause physical discomfort to the patient and produce other side effects.

[0004] In view of this, there is an urgent need to provide a new electric field generation solution to at least solve the defects of the above non-invasive solutions. Summary of the invention

[0005] In order to at least solve one or more of the technical problems mentioned above, the present disclosure proposes a solution of an electric field generating system and a method of use in multiple aspects.

[0006] In a first aspect, the present disclosure provides an electric field generating system, which includes a collection electrode and an electric field generating electrode, wherein the collection electrode is used to be implanted into the central area and / or peripheral area of ​​the target tissue to collect electrical signals from the target tissue and / or surrounding tissue; the electric field generating electrode is used to be implanted into the central area and / or peripheral area of ​​the target tissue to generate a target electric field to the target tissue.

[0007] In some embodiments, the implantation position of the electric field generating electrode is located outside the collecting electrode.

[0008] In other embodiments, the collection electrode includes at least one of a ring electrode, a directional electrode, and an umbrella-shaped electrode; and / or the dielectric constant of the electric field generating electrode is greater than the dielectric constant of the collection electrode; and / or the electric field generating electrode is an insulating electrode; and / or the outer tube of the electric field generating electrode is one or more of barium titanate, lead niobate, lithium niobate, polyvinylidene fluoride, polytetrafluoroethylene, and ceramic materials.

[0009] In some other embodiments, the electric field generating electrode includes a first electrode. When there is a cavity in the target tissue, the first electrode is used to be implanted into the cavity together with the charge storage material, so that the charge storage material contacts both the first electrode and the target tissue.

[0010] In some embodiments, the electric field generating electrode further comprises a second electrode, and the second electrode is adapted to be implanted into a peripheral region of the target tissue.

[0011] In other embodiments, the electric field generating electrode includes an outer tube, a wire and a metal layer; the wire and the metal layer are both located inside the outer tube, and the metal layer is wound around the wire to form a winding structure.

[0012] In some further embodiments, the electric field generating electrode is divided into a plurality of electrode segments along its radial direction and / or axial direction, wherein each electrode segment is connected to a corresponding wire.

[0013] In some embodiments, the electric field generating system includes multiple groups of electric field generating electrode pairs, each group of electric field generating electrode pairs includes two electric field generating electrodes implanted on both sides of the target tissue, and the multiple groups of electric field generating electrode pairs form an angle of 45° to 90° with each other.

[0014] In other embodiments, a temperature sensor is integrated on the electric field generating electrode; and / or the electric field generating electrode and / or the collection electrode have a developing marker that can be imaged in medical images; and / or a cooling channel is provided inside the tube wall of the outer tube of the electric field generating electrode and / or on the inner side of the outer tube of the electric field generating electrode.

[0015] In some further embodiments, the electric field generating system also includes an electric field generator, which includes a monitoring module, a control module and a suppression module; wherein the monitoring module is used to receive the electric signal collected by the collection electrode to monitor the growth of the target tissue; the control module is used to determine whether to generate a target electric field to the target tissue and / or adjust the electric field parameters of the target electric field according to the growth condition; and the suppression module is used to output a corresponding electric field signal to the target electric field generating electrode in response to receiving an electric field generation instruction to generate a target electric field and / or the electric field parameters.

[0016] In some embodiments, the electric field generating system further comprises a programmable device disposed outside the body for controlling the collection electrodes, the electric field generating electrodes, and / or the electric field generator.

[0017] In other embodiments, the monitoring module and / or the programmable device are further used to: construct a conductivity distribution map of the target tissue and / or the surrounding tissue based on the collected electrical signals; and monitor the growth of the target tissue according to the conductivity distribution map.

[0018] In some other embodiments, the control module and / or the programmable control device is also used to: determine the electric field strength of the target electric field generated to the target tissue according to the growth stage of the target tissue; wherein in response to the target tissue being in an early stage where cell division is inactive, the electric field strength is determined to be 1V / cm to 2.25V / cm; in response to the target tissue being in a progressive stage where cell division is active, the electric field strength is determined to be greater than 2.25V / cm.

[0019] In some embodiments, the electric field generating system also includes an implantable ultrasonic sensor, which is used to be implanted in the peripheral area of ​​the target tissue; the ultrasonic sensor includes an ultrasonic transmitting unit and an ultrasonic receiving unit, wherein the ultrasonic transmitting unit is used to transmit ultrasonic pulses to the target tissue and / or surrounding tissue; the ultrasonic receiving unit is used to receive ultrasonic pulses reflected back from the target tissue and / or surrounding tissue, and convert the reflected ultrasonic pulses into ultrasonic electrical signals; the programmable device is also used to generate an ultrasonic image of the target tissue and / or surrounding tissue based on the ultrasonic electrical signals.

[0020] In a second aspect, the present disclosure provides a method for using an electric field generating system, comprising using the electric field generating system described in any one of the first aspects of the present disclosure to generate a target electric field to a target tissue.

[0021] In some embodiments, before using the electric field generating system to generate a target electric field to the target tissue, the method of use also includes: using laser ablation technology to ablate the target tissue so as to use the electric field generating system to generate a target electric field to the ablated target tissue.

[0022] Through the electric field generating system provided above, by setting up an implantable collection electrode and an implantable electric field generating electrode, it is not only easy to carry by the biological body and avoid stimulation of the biological body surface (such as the scalp), but also has the functions of collecting electrical signals and generating a target electric field at the same time. The two electrodes are used to realize different functions respectively, so that the two electrodes do not interfere with each other and can work at the same time. BRIEF DESCRIPTION OF THE DRAWINGS

[0023] By reading the detailed description below with reference to the accompanying drawings, the above and other objects, features and advantages of the exemplary embodiments of the present disclosure will become readily understood. In the accompanying drawings, several embodiments of the present disclosure are shown in an exemplary and non-limiting manner, and the same or corresponding reference numerals represent the same or corresponding parts, wherein:

[0024] Figure 1 A schematic diagram showing an electric field generating system according to some embodiments of the present disclosure;

[0025] Figure 2a A schematic diagram showing the structure of an electric field generating electrode according to some embodiments of the present disclosure;

[0026] Figure 2b Shows Figure 2a A schematic top view of the electric field generating electrode shown;

[0027] Figure 3a A schematic diagram showing an electric field generating electrode divided into a plurality of electrode segments along a radial direction according to some embodiments of the present disclosure;

[0028] Figure 3b Show Figure 3a A schematic top view of the electric field generating electrode shown;

[0029] Figure 4 A schematic diagram showing an electric field generating electrode divided into a plurality of electrode segments along an axial direction according to an embodiment of the present disclosure;

[0030] Figure 5a A schematic diagram showing an application scenario of an electric field generating system including a first electrode according to some embodiments of the present disclosure;

[0031] Figure 5b A schematic diagram showing an application scenario of an electric field generating system including a second electrode according to some embodiments of the present disclosure;

[0032] Figure 6 A schematic top view of an electric field generating system including a plurality of collecting electrodes and a plurality of electric field generating electrodes according to some embodiments of the present disclosure is shown;

[0033] Figure 7 A schematic block diagram showing an electric field generating system including an electric field generator according to an embodiment of the present disclosure;

[0034] Figure 8 A schematic block diagram of an electric field generating system including a program-controlled device according to an embodiment of the present disclosure is shown. DETAILED DESCRIPTION

[0035] The following will be combined with the drawings in the embodiments of the present disclosure to clearly and completely describe the technical solutions in the embodiments of the present disclosure. Obviously, the described embodiments are part of the embodiments of the present disclosure, not all of the embodiments. Based on the embodiments in the present disclosure, all other embodiments obtained by those skilled in the art without creative work are within the scope of protection of the present disclosure.

[0036] It should be understood that the terms "include" and "comprising" used in the specification and claims of the present disclosure indicate the presence of described features, integers, steps, operations, elements and / or components, but do not exclude the presence or addition of one or more other features, integers, steps, operations, elements, components and / or collections thereof.

[0037] It should also be understood that the terms used in this disclosure are only for the purpose of describing specific embodiments and are not intended to limit the disclosure. As used in this disclosure and claims, the singular forms of "a", "an", and "the" are intended to include the plural forms unless the context clearly indicates otherwise. It should also be further understood that the term "and / or" used in this disclosure and claims refers to any combination of one or more of the associated listed items and all possible combinations, including these combinations.

[0038] As used in this specification and claims, the term "if" may be interpreted as "when" or "upon" or "in response to determining" or "in response to detecting," depending on the context. Similarly, the phrase "if it is determined" or "if [described condition or event] is detected" may be interpreted as meaning "upon determination" or "in response to determining" or "upon detection of [described condition or event]" or "in response to detecting [described condition or event]," depending on the context.

[0039] The specific implementation of the present disclosure is described in detail below with reference to the accompanying drawings.

[0040] Figure 1 Schematic diagram of an electric field generating system according to some embodiments of the present disclosure is shown. Figure 1 As shown in the figure, the electric field generating system includes a collection electrode 110 and an electric field generating electrode 120, wherein the collection electrode 110 can be used to be implanted into the central area 11 and / or the peripheral area 12 (for example, the range shown by the dotted line) of the target tissue 10 to collect electrical signals from the target tissue 10 and / or the surrounding tissues; the electric field generating electrode 120 can be used to be implanted into the central area 11 and / or the peripheral area 12 of the target tissue 10 to generate a target electric field to the target tissue 10.

[0041] In some application scenarios, the target tissue 10 may be a target lesion tissue in a living body, such as a tumor, or other lesion tissue that requires electric field stimulation or electric field treatment. The living body may include a human body, an animal body, etc. The surrounding tissue may be a tissue located around the target tissue, such as a tissue located in the peripheral area 12, and the surrounding tissue may be a healthy tissue of the living body. The central area 11 of the target tissue 10 may be an area near the center of the target tissue 10, and the peripheral area 12 may be an area outside the target tissue 10 near the edge of the target tissue 10.

[0042] In some embodiments, the number of the collection electrodes 110 may be one or more, and each collection electrode 110 may have one or more electrode contacts. One or more collection electrodes 110 may be used to be implanted in the central area 11 or the peripheral area 12 of the target tissue 10. In the case of setting multiple collection electrodes 110, the multiple collection electrodes 110 may also be respectively set in the central area 11 and the peripheral area 12. In some embodiments, the electrical signals collected by the collection electrode 110 may include bioelectric signals, such as brain electroencephalogram signals, electrocardiogram signals, etc. In other embodiments, the collection electrode 110 may apply a weak AC signal (usually in the range of kHz to MHz), and then collect electrical signals of the target tissue and / or surrounding tissue through the electrode contacts, and the electrical signals may include current or voltage drop, etc. In some embodiments, the collection electrode 110 may include at least one of a ring electrode, a directional electrode, an umbrella electrode, etc. When the collection electrode 110 is a directional electrode, the direction of the collected electrical signal can be determined.

[0043] In other embodiments, the number of the electric field generating electrodes 120 may be one or more. The one or more electric field generating electrodes 120 may be used to be implanted in the central area 11 or the peripheral area 12 of the target tissue 10. In the case of providing multiple electric field generating electrodes 120, the multiple electric field generating electrodes 120 may also be provided in the central area 11 and the peripheral area 12, respectively. In some application scenarios, when the electric field generating electrode 120 is provided only in the central area 11 of the target tissue 10, the electric charge may be transmitted to the target tissue 10 through the electric field generating electrode 120, so that the growth of the target tissue 10 may be inhibited. In other application scenarios, when the number of the electric field generating electrodes 120 is multiple, every two electric field generating electrodes 120 may form a group of electric field generating electrode pairs, so as to generate an electric field in one direction between each group of electric field generating electrode pairs.

[0044] The target electric field mentioned above may include an electric field covering the entire target tissue 10, or an electric field covering a partial area of ​​the target tissue 10. The number and implantation position of the electric field generating electrodes 120 may be determined according to factors such as the size, shape, and growth stage of the target tissue 10. For example, the target electric field may be set with the purpose of covering the entire target tissue 10. The larger the size of the target tissue 10, the more electric field generating electrodes 120 are set, and the smaller the size of the target tissue 10, the fewer electric field generating electrodes 120 are set.

[0045] In some embodiments, the dielectric constant of the electric field generating electrode 120 is greater than the dielectric constant of the collection electrode 110. Therefore, compared with the collection electrode 110, the electric field generating electrode 120 has a stronger charge storage capacity. In other embodiments, the electric field generating electrode 120 can be made of a high dielectric constant material, for example, the outer tube of the electric field generating electrode 120 can be one or more of barium titanate, lead niobate, lithium niobate, polyvinylidene fluoride, polytetrafluoroethylene, ceramic materials, etc. For example, in some other embodiments, the outer tube of the electric field generating electrode 120 is a PTZ ceramic (or piezoelectric ceramic) material. According to such a setting, the electric field generating electrode 120 can not only be used to generate an electric field, but also can be conducive to maintaining a high-intensity electric field due to its strong charge storage capacity, thereby optimizing the generation efficiency of the electric field.

[0046] In other embodiments, the electric field generating electrode 120 may be an insulated electrode. Compared with a conductive electrode, an insulated electrode will not stimulate nerve tissue and cause the organism to feel an electric shock. In particular, if the outer tube of the electric field generating electrode 120 is made of a material with a high dielectric constant and a good insulator (such as barium titanate, polytetrafluoroethylene, etc.), the electric field generating electrode 120 has the characteristics of both safety and enhanced electric field strength.

[0047] In some other embodiments, the collection electrode 110 and / or the electric field generating electrode 120 may be made of a flexible material so as to be formed into a desired shape, thereby being more adaptable to irregular implantation positions and / or target tissues of specific shapes, and being conducive to avoiding damage to surrounding tissues during implantation. In some embodiments, the surface of the collection electrode 110 and / or the electric field generating electrode 120 may be coated with a material coating that promotes biointegration, such as a hydrogel or a specific biomolecule, to reduce foreign body reactions and enhance adhesion between the electrode and tissue.

[0048] In some embodiments, a temperature sensor may be integrated on the electric field generating electrode 120 to sense the temperature of the electric field generating electrode 120; and / or, the electric field generating electrode 120 and / or the collection electrode 110 may have a developing marker that can be imaged in medical images; and / or, a cooling channel may be provided inside the tube wall of the outer tube of the electric field generating electrode 120 and / or on the inner side of the outer tube of the electric field generating electrode 120.

[0049] The number of temperature sensors may be one or more. The temperature sensor may be disposed at a position such as the end of the electric field generating electrode 120, or the electric field generating region of the electric field generating electrode 120. The wall of the outer tube of the electric field generating electrode 120 may have a certain thickness, so that one or more cooling channels may be disposed in the wall. A cooling channel may be formed between the inner side of the outer tube of the electric field generating electrode 120 and the electric field generating component (such as the metal layer and the wire described below). When there are cooling channels in the wall of the outer tube of the electric field generating electrode 120 and the inner side of the outer tube of the electric field generating electrode 120, one of the cooling channels may be used as a cooling medium inflow channel, and the other cooling channel may be used as a cooling medium outflow channel. The cooling medium may include a coolant, a cooling gas, or the like. By providing a cooling channel, when the temperature of the electric field generating electrode 120 is too high, the heat generated by the electric field generating electrode 120 may be absorbed by the cooling medium circulating in the cooling channel, so as to effectively avoid tissue damage that may be caused by overheating of the tissue around the electric field generating electrode 120.

[0050] The imaging markers described above may be non-ferromagnetic materials and may be compatible with medical imaging detection such as magnetic resonance imaging (MRI) and computed tomography (CT), so that the electric field generating electrode 120 and / or the collection electrode 110 can be visualized in medical images. The imaging markers may be ring-shaped, sheet-shaped, circular, square or other regular or irregular shapes. One or more imaging markers may be provided on each electrode.

[0051] Combination of the above Figure 1 The electric field generating system according to some embodiments of the present disclosure is described in an exemplary manner. It is understood that the above description is exemplary and not restrictive. For example, the number of the collecting electrode 110 and / or the electric field generating electrode 120 may not be limited to one as shown in the figure, and more may be provided as needed. For another example, the electric field generating electrode 120 may not be limited to only having an outer tube of a high dielectric constant material, but may also include other components for transmitting electric field signals. For ease of understanding, the following will be combined with Figure 2a-Figure 4 An exemplary description is given.

[0052] Figure 2a A schematic diagram showing the structure of an electric field generating electrode according to some embodiments of the present disclosure. Figure 2b Shows Figure 2a Schematic diagram of the top view of the electric field generating electrode shown in FIG. Figure 2a and Figure 2b As shown in , the electric field generating electrode 120 may include an outer tube 121, a wire 122 and a metal layer 123; wherein the wire 122 and the metal layer 123 are both located in the outer tube 121, and the metal layer 123 may be wound around the wire 122 to form a winding structure.

[0053] The metal layer 123 can be in the form of a sheet, which contacts the wire 122 and is wound around the wire 122, thereby forming a larger contact area, which is conducive to transferring more charges to the outer tube 121, and is conducive to further improving the effect of maintaining the electric field strength. In some embodiments, the electric field generating electrode 120 configured in this way can be positively charged or negatively charged throughout. In other embodiments, the open end of the outer tube of the electric field generating electrode 120 can be sealed by a component such as a sealing plug. In some embodiments, the metal layer 123 can include one or more of metals such as gold and copper.

[0054] Understandably, Figure 2a and Figure 2b The structure of the electric field generating electrode shown is exemplary and not restrictive. For example, the electric field generating electrode 120 may not be limited to the full-body structure shown in the figure, but may also have a segmented structure. Figure 3a to Figure 4 An exemplary description is given.

[0055] Figure 3a A schematic diagram showing an electric field generating electrode divided into a plurality of electrode segments along a radial direction according to some embodiments of the present disclosure. Figure 3b Show Figure 3a Schematic diagram of the top view of the electric field generating electrode shown in FIG. Figure 3a and Figure 3b As shown in , the electric field generating electrode 120 can be separated into a plurality of electrode segments (such as the first electrode segment 211 and the second electrode segment 212 shown in the figure) along its radial direction R, wherein each electrode segment can be connected to a corresponding wire. For example, the first electrode segment 211 shown in the figure is connected to the first wire 122-1, and the second electrode segment 212 can be connected to the second wire 122-2. A corresponding metal layer can be provided in each electrode segment to contact the corresponding wire. For example, as further shown in the figure, in the first electrode segment 211, the first metal layer 123-1 can contact the first wire 122-1 and be wound around the first wire 122-1 to form a winding structure; in the second electrode segment 212, the second metal layer 123-2 can contact the second wire 122-2 and be wound around the second wire 122-2 to form a winding structure. Multiple electrode segments can be separated by, for example, cavities or non-charge storage materials or other isolation structures.

[0056] It is understandable that, through such a configuration, different electrode segments of the electric field generating electrode 120 can carry different charges, for example, the first electrode segment 211 carries a positive charge, and the second electrode segment 212 carries a negative charge, so that it can be used to achieve target electric fields in more directions and shapes. At the same time, for each electrode segment, a large contact area between the metal layer and the corresponding wire can still be ensured, thereby still ensuring the effect of maintaining the electric field strength of the electric field generating electrode.

[0057] Figure 4 FIG. 2 is a schematic diagram showing an electric field generating electrode divided into a plurality of electrode segments along the axial direction according to an embodiment of the present disclosure. Figure 4 As shown in , the electric field generating electrode 120 can be separated into a plurality of electrode segments (such as the first electrode segment 211 and the second electrode segment 212 shown in the figure) along its axial direction A, wherein each electrode segment can be connected to a corresponding wire. For example, the first electrode segment 211 shown in the figure is connected to the first wire 122-1, and the second electrode segment 212 can be connected to the second wire 122-2. A corresponding metal layer can be provided in each electrode segment to contact the corresponding wire. For example, in the first electrode segment 211, the first metal layer (not shown) can contact the first wire 122-1 and be wound around the first wire 122-1 to form a winding structure; in the second electrode segment 212, the second metal layer (not shown) can contact the second wire 122-2 and be wound around the second wire 122-2 to form a winding structure. Multiple electrode segments can be separated by, for example, cavities or non-charge storage materials or other isolation structures.

[0058] It is understandable that, through such a configuration, different electrode segments of the electric field generating electrode 120 can carry different charges, for example, the first electrode segment 211 carries a positive charge, and the second electrode segment 212 carries a negative charge, thereby being used to achieve target electric fields in more directions and shapes.

[0059] Combination of the above Figure 3a-Figure 4 An exemplary description is given of an electric field generating electrode including electrode segments according to an embodiment of the present disclosure. It is to be understood that the structure shown in the figure is exemplary and not restrictive. For example, the number of electrode segments may not be limited to the two shown in the figure, and more may be provided as needed. For another example, the segmentation direction may not be limited to only the radial direction R or the axial direction A shown in the figure, and may also be separated in both the radial direction R and the axial direction A as needed to obtain more electrode segments, for example, electrode segments distributed in an array may be obtained.

[0060] Figure 5a Schematic diagram of application scenarios of an electric field generating system including a first electrode according to some embodiments of the present disclosure is shown. Figure 5aAs shown in , the electric field generating electrode may include a first electrode 501. When there is a cavity 13 in the target tissue 10, the first electrode 501 is used to be implanted into the cavity 13 together with a charge storage material, and the charge storage material is in contact with both the first electrode 501 and the target tissue 10.

[0061] In some scenarios, the target tumor is debulked by debulking surgery or ablation surgery, and the target tumor will leave a debulking cavity, and the periphery or part of the periphery of the debulking cavity has uncut / unablated tumor. That is, in this embodiment, the target tissue 10 can be the target tumor, the cavity 13 can be the debulking cavity, and other areas of the target tissue 10 except the cavity 13 can be uncut / unablated tumor.

[0062] In some embodiments, the number of the first electrodes 501 implanted into the cavity 13 may be one or more. A flexible charge storage material and at least one first electrode 501 may be implanted in the cavity 13, and the charge storage material may be in contact with the first electrode 501 and the target tissue 10, respectively. For example, the charge storage material may be filled between the first electrode 501 and the target tissue 10. For another example, the first electrode 501 and the charge storage material are both in contact with the target tissue 10, and the charge storage material is in contact with the first electrode 501 at the same time. In other embodiments, the charge storage material may include, for example, one or more of polyvinylidene fluoride (PVDF), polytetrafluoroethylene, polypyrrole (PPy), polyaniline (PANI), or other flexible materials with a high dielectric constant.

[0063] In e.g. Figure 5a In the illustrated embodiment, the first electrode 501 can directly release charges to the charge storage material, and the charge storage material can be in contact with the target tissue 10 to transfer the charges to the target tissue 10, thereby inhibiting the division of the target tissue 10. In this case, the purpose of releasing charges to the target tissue 10 can be achieved only by implanting the first electrode 501 in the cavity 13, which is beneficial to reducing the energy consumption of the system and achieving energy saving.

[0064] It can be understood that the electric field generating electrode according to the embodiment of the present disclosure may not be limited to only including the first electrode 501, but may also include a second electrode. Figure 5b An exemplary description is given.

[0065] Figure 5b Schematic diagram of application scenarios of an electric field generating system including a second electrode according to some embodiments of the present disclosure is shown. Figure 5bAs shown in , the electric field generating electrode may include a first electrode 501 and a second electrode 502. When there is a cavity 13 in the target tissue 10, the first electrode 501 is used to be implanted into the cavity 13 together with the charge storage material, and the charge storage material is in contact with both the first electrode 501 and the target tissue 10, and the second electrode 502 is used to be implanted into the peripheral area 12 of the target tissue 10. The number of the second electrode 502 may be one or more.

[0066] Through the target electric field formed between the first electrode 501 and the second electrode 502, the charge storage material can store charges in the field strength in the target electric field, and through the charge storage material contacting the target tissue 10, the charges stored in the charge storage material can be transferred and applied to the target tissue 10 to inhibit the growth of the target tissue 10.

[0067] It is understandable that the above combination Figure 5a and Figure 5b The description is exemplary and not restrictive. For example, it is not limited to implanting the first electrode 501 and the charge storage material into the cavity 13 together. It is also possible to implant only the first electrode 501 into the cavity 13, and release the charge directly to the target tissue 10 through the contact between the first electrode 501 and the target tissue 10, or through the target electric field formed by the first electrode 501 and the second electrode 502, so as to achieve the purpose of inhibiting the growth of the target tissue. For example, only the charge storage material can be implanted in the cavity 13, and a plurality of second electrodes can be arranged on both sides of the target tissue 10, so that the target electric field formed between the plurality of second electrodes can cover the area where the target tissue is located, so that the charge storage material can store the charge and transfer the charge to the target tissue. In addition, it can be understood that Figure 5a and Figure 5b The electric field generating system according to the embodiment of the present disclosure further includes a collecting electrode. Figure 6 An exemplary description is given of a case where a plurality of collection electrodes and a plurality of electric field generating electrodes are implanted in the peripheral area 12 according to an embodiment of the present disclosure.

[0068] Figure 6 FIG. 1 is a schematic top view of an electric field generating system including a plurality of collecting electrodes and a plurality of electric field generating electrodes according to some embodiments of the present disclosure. Figure 6 As shown in , the electric field generating system according to the embodiment of the present disclosure may include a plurality of collecting electrodes 110 and a plurality of electric field generating electrodes 120 , and the plurality of collecting electrodes 110 and the plurality of electric field generating electrodes 120 may be implanted into the peripheral area of ​​the target tissue 10 .

[0069] An appropriate spacing D should be maintained between the multiple electric field generating electrodes 120. Generally speaking, the electric field strength in the area between the two electric field generating electrodes 120 is appropriate, but near the electric field generating electrodes 120, the electric field strength will increase with the increase of the power supply voltage. Therefore, the spacing between the multiple electric field generating electrodes 120 has a significant impact on the electric field strength, and the distribution of the multiple electric field generating electrodes 120 needs to maintain an appropriate spacing D to ensure the uniform distribution of the target electric field in the area where the target tissue 10 is located, avoid areas where the electric field is too strong or too weak, and avoid heat dissipation problems and safety risks that may be caused by too close spacing. According to the output power of the electric field generating electrode 120 and the field strength requirement of the target electric field, the minimum spacing between the two electric field generating electrodes 120 can be determined, so that the positions of the multiple electric field generating electrodes 120 can be arranged according to the minimum spacing to ensure that the spacing D between every two electric field generating electrodes 120 is greater than the minimum spacing.

[0070] In some embodiments, the implantation position of the electric field generating electrode 120 may be located at the periphery of the collection electrode 110. Here, the electric field generating electrode 120 is located at the periphery of the collection electrode 110, and may be located at the outside of the collection electrode 110. In other embodiments, the collection electrode 110 may be located between the electric field generating electrode 120 and the target tissue 10. According to such a setting, it is beneficial for the collection electrode 110 to accurately collect electrical signals, and it is also possible to keep a sufficient distance between the electric field generating electrode 120 and the target tissue 10, so as to avoid the problem of uneven field strength distribution in the area where the target tissue 10 is located, which may be caused by the target tissue 10 being too close to the electric field generating electrode 120.

[0071] In other embodiments, the electric field generating system may include multiple groups of electric field generating electrode pairs, each group of electric field generating electrode pairs may include two electric field generating electrodes implanted on both sides of the target tissue 10, and the multiple groups of electric field generating electrode pairs may form an angle of 45° to 90° with each other. An electric field in one direction is formed between each group of electric field generating electrode pairs, and a target electric field covering the target tissue 10 is formed between the multiple groups of electric field generating electrode pairs.

[0072] like Figure 6 It is further shown that it is assumed that the electric field generating system may include three groups of electric field generating electrode pairs, for example a first group of electric field generating electrode pairs 601, a second group of electric field generating electrode pairs 602 and a third group of electric field generating electrode pairs 603, wherein the first group of electric field generating electrode pairs 601 includes two electric field generating electrodes located on both sides of the target tissue 10 in the direction indicated by the arrows in the figure, the second group of electric field generating electrode pairs 602 includes two electric field generating electrodes located on both sides of the target tissue 10 in the direction indicated by the arrows in the figure, and the third group of electric field generating electrode pairs 603 includes two electric field generating electrodes located on both sides of the target tissue 10 in the direction indicated by the arrows in the figure.

[0073] Further, a first angle α1 may be formed between the first group of electric field generating electrode pairs 601 and the second group of electric field generating electrode pairs 602, a second angle α2 may be formed between the second group of electric field generating electrode pairs 602 and the third group of electric field generating electrode pairs 603, and a third angle α3 may be formed between the third group of electric field generating electrode pairs 603 and the first group of electric field generating electrode pairs 601. The angles formed between multiple groups of electric field generating electrode pairs are the angles formed between the straight lines where the multiple groups of electric field generating electrode pairs are arranged. In some embodiments, the first angle α1 may be 90°, the second angle α2 may be 45°, and the third angle α3 may be 45°. In other embodiments, the first angle α1, the second angle α2, and the third angle α3 may be 60° to each other.

[0074] Combination of the above Figure 6 An exemplary description is given of an electric field generating system including a plurality of electric field generating electrodes according to an embodiment of the present disclosure. It can be understood that by setting a plurality of groups of electric field generating electrode pairs at an angle of 45° to 90° to each other, the distribution of the target electric field can be made more uniform, and it is helpful to determine the number of electric field generating electrodes required for the target electric field to cover the target tissue, and it can also ensure that the spacing D between adjacent electric field generating electrodes 120 can be maintained at an appropriate distance. By setting the electric field generating electrodes at the periphery of the collection electrode, especially when multiple groups of electric field generating electrode pairs are set, it can be helpful to maintain the spacing between the two electric field generating electrodes in each group of electric field generating electrode pairs at an appropriate distance, so that the target tissue 10 can be located in the area where the field strength of the target electric field is evenly distributed, rather than being close to a certain electric field generating electrode, which causes the problem of uneven field strength received by the target tissue 10.

[0075] It can also be understood that the above description is exemplary rather than restrictive. For example, the number of collection electrodes may not be limited to the five shown in the figure, and may be set more or less as needed. The number of electric field generating electrode pairs may not be limited to the three groups shown in the figure, and may be set more or less as needed. It should be noted that studies have shown that the electric field inhibition effect is strongest when the direction of the electric field is parallel to the cell division axis. However, since the polarity of tumor cells during the division cycle is irregular, applying electric fields in different directions is an effective way to increase the inhibitory effect. That is, the arrangement of electric field generating electrode pairs in multiple directions can more effectively inhibit the mitosis of tumor cells. Compared with only one set of electric field generating electrode pairs and two sets of electric field generating electrode pairs, the target electric field formed by setting three or more sets of electric field generating electrode pairs has more directions and a wider distribution range of the electric field, and the inhibitory effect on the target tissue will be more significant.

[0076] Furthermore, the electric field generating system of the embodiment of the present disclosure may not be limited to only including the aforementioned collecting electrodes and electric field generating electrodes, but may also include other devices or equipment. Figure 7 Provide further explanation.

[0077] Figure 7 Schematic block diagram of an electric field generating system including an electric field generator according to an embodiment of the present disclosure is shown. Figure 7 As shown in , the electric field generating system may include a collection electrode 110, an electric field generating electrode 120 and an electric field generator 710, wherein the electric field generator 710 may include a monitoring module 711, a control module 712 and a suppression module 713; the monitoring module 711 may be used to receive the electric signal collected by the collection electrode 110 to monitor the growth of the target tissue; the control module 712 may be used to determine whether to generate a target electric field to the target tissue and / or adjust the electric field parameters of the target electric field according to the growth of the target tissue; the suppression module 713 may be used to output a corresponding electric field signal to the target electric field generating electrode 120 in response to receiving an electric field generation instruction and / or electric field parameters for generating a target electric field.

[0078] The electric field generator 710 may be implantable and may be connected to the collection electrode 110 and the electric field generating electrode 120, respectively. Different types of tissues and organs have different electrical conductivities (i.e., electrical conductivity). For example, blood, muscle, and certain tumor tissues generally have higher electrical conductivity than fat, bone, or air in the lungs. Since tumor growth may cause changes in dielectric constant and conductivity, changes in target tissues (e.g., tumors) may be monitored in real time based on this principle. In some embodiments, the growth of the target tissue may include, for example, one or more of the growth direction, rate, size, shape, growth stage, cell active area, tissue type, growth location, and the like of the target tissue.

[0079] Specifically, a weak alternating current of known amplitude and frequency is applied to the body through the electrode contacts of the collection electrode 110 implanted in the body, and the voltage drop (or potential difference, voltage value) between the electrode contacts of the collection electrode 110 can be measured to calculate information such as conductivity and resistance. Due to the different conductivity of biological tissues, the distribution of current in the body will be affected, resulting in changes in the measured voltage value. Based on the collected voltage value and the known applied current, an impedance analyzer can be used in vitro to measure the impedance at different frequencies to obtain more information about the conductivity and dielectric constant of the target tissue. The measurement of resistance and impedance can provide information about tissue properties (such as water content, ion concentration, etc.).

[0080] In some embodiments, the monitoring module 711 can also be used to: construct a conductivity distribution map of the target tissue and / or surrounding tissue based on the collected electrical signals; and monitor the growth of the target tissue according to the conductivity distribution map. Since the collection electrode 110 can be used to be implanted in the central area and / or peripheral area of ​​the target tissue, especially when the collection electrode 110 uses a directional electrode, it can collect electrical signals such as the target tissue and the surrounding tissue in its peripheral area, as well as voltage drops in multiple directions, so that the conductivity of the target tissue and / or surrounding tissue can be determined based on the electrical signals. By analyzing the conductivity data, the conductivity changes caused by the growth of the target tissue can be identified, so that the purpose of monitoring the growth of the target tissue can be achieved.

[0081] In some embodiments, the conductivity distribution map can be updated in real time according to the changes in the collected electrical signals, so as to realize real-time monitoring of the growth of the target tissue according to the conductivity distribution map. In other embodiments, the conductivity distribution map can be two-dimensional or three-dimensional. In some other embodiments, the conductivity distribution map can be a contour map, that is, the connection lines of points with the same conductivity are displayed by contour lines (contour lines), which can help identify the pattern and trend of conductivity changes. In other embodiments, the conductivity distribution map can also be a multimodal fusion map, for example, by fusing conductivity data with parameters such as electric field strength and temperature, the conductivity distribution map formed can simultaneously display the spatial distribution of multiple parameters.

[0082] In some embodiments, the conductivity distribution map can be a conductivity thermogram, and different levels of conductivity can be represented by color changes; for example, darker areas represent areas with higher conductivity, while lighter areas represent areas with lower conductivity. In other embodiments, the electrode space (i.e., the coordinate system where the acquisition electrode 110 is located) can be mapped to the medical image space (i.e., the coordinate system of nuclear magnetic resonance, CT images, etc.), and the mapped conductivity data can be used to generate a conductivity thermogram of the target tissue and / or surrounding tissue to accurately display the conductivity differences at different locations of the target tissue and / or surrounding tissue, which will be more helpful in intuitively displaying the growth of the target tissue and the spatial distribution of the electric field effect.

[0083] In some embodiments, the control module 712 can be implemented in the form of a microcontroller (MCU) or a digital signal processor (DSP). In other embodiments, the control module 712 can include a PID controller or other types of control logic. In some other embodiments, the control module 712 determines whether to generate a target electric field to the target tissue according to the growth of the target tissue, which can include: in response to a change in the growth of the target tissue, it can be determined that the target electric field is generated to the target tissue; in response to the growth of the target tissue not changing, it can be determined that the target electric field is not generated to the target tissue. In other embodiments, the control module 712 can determine whether to adjust the electric field parameters of the target electric field according to the growth of the target tissue, where the electric field parameters can include electric field direction, electric field strength, frequency, waveform, etc. For example, assuming that it is monitored that the target tissue grows faster in a certain direction, the control module 712 can adjust the electric field strength of the target electric field in the corresponding direction, or control the electric field generating electrode in the corresponding direction to generate an electric field to inhibit the growth of the target tissue in the corresponding direction, while also avoiding damage to other normal tissues.

[0084] It should be understood that different electric field strengths, frequencies and waveforms are required for cells or lesions of different types / growth locations. Certain types of cancer cells may be more sensitive to AC electric fields of specific frequencies. For example, non-small cell lung cancer (NSCLC) responds best to a frequency of 150kHz; breast cancer responds best to a frequency of 150kHz; pancreatic cancer responds best to a frequency of 150kHz; ovarian cancer responds best to a frequency of 200kHz; glioblastoma multiforme (GBM) responds best to a frequency of 200kHz; malignant pleural mesothelioma (MPM) is suppressed at 150kHz or 200kHz in most cases; cervical cancer responds best to a frequency of 120kHz. Therefore, according to the tissue type / growth location of the target tissue, the control module 712 can determine the electric field parameters of the target electric field.

[0085] It is also necessary to understand that studies have shown that within a certain range, as the electric field strength increases, the inhibitory effect on tumor cells gradually increases. When the electric field strength is greater than 1.0V / cm, the inhibitory effect on mitosis begins to appear, and when the strength is greater than 2.25V / cm, mitosis is completely inhibited. Based on this, in some other embodiments, the control module 712 can also be used to: determine the electric field strength of the target electric field generated to the target tissue according to the growth stage of the target tissue; wherein in response to the target tissue being in the early stage of inactive cell division, the electric field strength of the target electric field is determined to be 1V / cm to 2.25V / cm; in response to the target tissue being in the progressive stage of active cell division, the electric field strength of the target electric field is determined to be greater than 2.25V / cm.

[0086] Specifically, in response to the target tissue being in an early stage where cell division is inactive, it can be determined to use a target electric field with a lower electric field strength to inhibit or maintain the target tissue; in response to the target tissue being in a progressive stage where cell division is active, at this stage, the target tissue cells (such as tumor cells) continue to proliferate and may begin to invade surrounding tissues. At this time, since the target tissue cells are in an actively dividing state, their sensitivity to electric field therapy increases, so it can be determined to use a target electric field with a higher electric field strength to inhibit the target tissue, so as to inhibit the mitosis of the target tissue and even cause apoptosis of the target tissue cells.

[0087] Further, the suppression module 713 can be used to respond to receiving an electric field generation instruction and / or electric field parameters for generating a target electric field, and output a corresponding electric field signal to the target electric field generating electrode 120. The electric field generating electrode 120 outputs a target electric field based on the electric field signal to suppress the target tissue.

[0088] In some other embodiments, the monitoring module 711 can also be used to record the electric field wave signal through the acquisition electrode 110 when the electric field generating electrode 120 generates the target electric field. By synchronously recording the electric field wave signal such as the current parameter when the target electric field occurs, and based on the electric field wave signal and the growth of the target tissue and other data, the stimulation effect of the target electric field on the target tissue can be monitored in real time. The control module 712 can adjust the electric field parameters according to the changes of the target tissue under the action of the target electric field to optimize the stimulation effect. Recording the electric field wave signal can help determine the distribution of the current in the target tissue, thereby improving the pertinence and accuracy of the electric field stimulation. This is particularly important for ensuring that the electric field energy effectively acts on the target area. By monitoring the electric field wave signal such as the current parameter, it can also ensure that the electric field stimulation is carried out within a safe parameter range to avoid tissue damage that may be caused by excessive stimulation.

[0089] Combination of the above Figure 7The electric field generating system according to other embodiments of the present disclosure is exemplarily described. It can be understood that the processing of data such as electric signals by the electric field generator 710 and the control of the electric field generating electrode 120 can realize adaptive regulation of the target electric field, thereby realizing closed-loop control of the electric field generating system. It can also be understood that the above description is exemplary and not restrictive. For example, the electric field generating system can also include an in vitro device. Figure 8 An exemplary description is given.

[0090] Figure 8 FIG. 1 is a schematic block diagram of an electric field generating system including a program-controlled device according to an embodiment of the present disclosure. Figure 8 As shown in , the electric field generating system may include an implantable device and an external device, wherein the implantable device may include a collection electrode 110, an electric field generating electrode 120 and an electric field generator 710, and the external device may include a program control device 810, and the program control device 810 is used to control the collection electrode 110, the electric field generating electrode 120, and / or the electric field generator 710. By controlling the collection electrode 110, the electric field generating electrode 120, and / or the electric field generator 710 through the program control device 810, the target electric field can be regulated according to the collected electrical signals, the growth of the target tissue and other information.

[0091] In some embodiments, the programmable device 810 can also be used to: construct a conductivity distribution map of the target tissue and / or surrounding tissue based on the collected electrical signals; and monitor the growth of the target tissue according to the conductivity distribution map. In other embodiments, the programmable device 810 can also be used to: determine the electric field strength of the target electric field generated to the target tissue according to the growth stage of the target tissue; wherein in response to the target tissue being in an early stage where cell division is inactive, the electric field strength is determined to be 1V / cm to 2.25V / cm; and in response to the target tissue being in a progressive stage where cell division is active, the electric field strength is determined to be greater than 2.25V / cm. These operations of the programmable device 810 are combined with the aforementioned Figure 7 The operations of the monitoring module 711 and the control module 712 are the same or similar, and are not described here. The electric field generator 710 and the program control device 810 can be used together to respectively realize closed-loop control and open-loop control of the target electric field according to the growth of the target tissue as needed.

[0092] In some other embodiments, the monitoring module 711 can also be used to monitor the temperature of the electric field generating electrode 120. In response to the temperature exceeding a preset threshold, the control module 712 and / or the programmable control device 810 can be triggered to issue an instruction to reduce the electric field strength of the target electric field, or to start a cooling operation.

[0093] In some embodiments, the program control device 810 may include a first communication module, and the electric field generator 710 may also include a second communication module, and the first communication module and the second communication module may be connected in communication to realize data transmission and interaction. In other embodiments, the first communication module and the second communication module may be implemented using wireless technologies such as low-power Bluetooth (BLE) or a low-speed short-distance transmission wireless network protocol (ZigBee). In some other embodiments, the program control device 810 may also include a data processing module for filtering, denoising, analyzing, processing, and other operations on the received data, such as processing the received electrical signal to construct a conductivity distribution map, etc. For example, the data processing module of the program control device 810 can establish a mathematical model based on historical data to predict the growth trend of the target tissue and the optimal parameters of the electric field effect, etc. For example, the data processing module of the program control device 810 can evaluate the influence of the electric field formed by different electric field parameters on the target tissue to determine the target electric field with the best effect.

[0094] In other embodiments, the program-controlled device 810 may include a power supply module, and the electric field generator 710 may include a power supply module, which may be rechargeable, and the power supply module may supply power to the battery module. In other embodiments, energy transmission may be achieved between the power supply module and the battery module through wireless charging methods such as coil induction. In some further embodiments, the in-vivo device may further include a charging interface, for example, the charging interface may be provided on the electric field generator 710, or connected to the electric field generator 710, and the charging interface may be exposed outside the body. In some embodiments, the charging interface may be magnetic or snap-on, and may be magnetically compatible.

[0095] Furthermore, in some other embodiments, the electric field generating system may also include an implantable ultrasonic sensor, which can be implanted in the peripheral area of ​​the target tissue; the ultrasonic sensor may include an ultrasonic transmitting unit and an ultrasonic receiving unit, wherein the ultrasonic transmitting unit can be used to transmit ultrasonic pulses to the target tissue and / or surrounding tissue; the ultrasonic receiving unit can be used to receive ultrasonic pulses reflected back from the target tissue and / or surrounding tissue, and convert the reflected ultrasonic pulses into ultrasonic electrical signals; the programmable control device 810 can also be used to generate an ultrasonic image of the target tissue and / or surrounding tissue based on the ultrasonic electrical signal.

[0096] In some embodiments, the implantable ultrasonic sensor can be a sensor based on an ultrasonic transducer of a piezoelectric ceramic. When a voltage pulse is applied to the piezoelectric ceramic, the ceramic sheet vibrates due to the inverse piezoelectric effect, generating ultrasonic pulses. That is, the ultrasonic transmitting unit transmits ultrasonic pulses, which can penetrate tissues and reflect when encountering interfaces of different densities. When the reflected ultrasonic pulse (i.e., ultrasonic echo) returns to the piezoelectric ceramic, the vibration of the ceramic sheet is converted into an ultrasonic electrical signal due to the positive piezoelectric effect. The ultrasonic receiving unit converts the reflected ultrasonic pulse into an ultrasonic electrical signal and transmits it to the program control device 810.

[0097] After the program control device 810 performs amplification and digitization processing on the ultrasonic electrical signal, a two-dimensional or three-dimensional ultrasonic image can be reconstructed. The ultrasonic image can display information such as the location, size, shape and boundary of the target tissue, so as to monitor the growth of the target tissue. The ultrasonic image can also be used in combination with other medical images (such as magnetic resonance imaging MRI, computer tomography CT, etc.), or can be fused with conductivity data to provide more comprehensive information about the target tissue, which is conducive to more accurate regulation of the target electric field.

[0098] In summary, the disclosed embodiments can simultaneously realize the functions of collecting electrical signals and generating target electric fields by setting collection electrodes and electric field generating electrodes. In some embodiments, the growth of target tissues is monitored according to the collected electrical signals, and the target electric field is regulated according to the growth of the monitored target tissues, which can not only achieve targeted inhibition of the growth of target tissues, but also accurately concentrate the inhibitory effect on target tissues in the desired area (for example, in the direction where the tumor grows faster), so that the inhibitory effect on the target tissue is highly targeted, avoiding excessive unnecessary effects on surrounding healthy tissues, so as to reduce the side effects and safety risks of electric field stimulation.

[0099] The present disclosure also provides a method for using an electric field generating system in another aspect, comprising using the above-mentioned method in combination with Figure 1-Figure 8 Any of the described electric field generating systems generates a target electric field toward a target tissue. For example, the collecting electrodes in the electric field generating system can be implanted into the central region and / or peripheral region of the target tissue to collect electrical signals from the target tissue and / or surrounding tissue; and the electric field generating electrodes in the electric field generating system can be implanted into the central region and / or peripheral region of the target tissue to generate a target electric field toward the target tissue.

[0100] In some embodiments, before using the electric field generating system to generate the target electric field to the target tissue, the method of use may further include: using laser ablation technology to ablate the target tissue so that the electric field generating system can generate the target electric field to the ablated target tissue. In other embodiments, after the target tissue is ablated using laser ablation technology, a cavity may be formed in the target tissue (if the target tissue is a tumor, the cavity may be a tumor reduction cavity), so that the collection electrode and / or the electric field generating electrode in the electric field generating system can be implanted into the cavity to generate the target electric field to the target tissue.

[0101] Although multiple embodiments of the present disclosure have been shown and described herein, it will be apparent to those skilled in the art that such embodiments are provided by way of example only. Those skilled in the art may think of many changes, modifications, and alternatives without departing from the thought and spirit of the present disclosure. It should be understood that in the process of practicing the present disclosure, various alternatives to the embodiments of the present disclosure described herein may be adopted. The attached claims are intended to define the scope of protection of the present disclosure, and therefore cover equivalents or alternatives within the scope of these claims.

Claims

1. An electric field generating system, comprising a collecting electrode and an electric field generating electrode, wherein: The collecting electrode is used to be implanted into the central area and / or the peripheral area of ​​the target tissue to collect electrical signals of the target tissue and / or the surrounding tissue; The electric field generating electrodes are used to be implanted into the central area and / or the peripheral area of ​​the target tissue to generate a target electric field toward the target tissue.

2. The electric field generating system according to claim 1, wherein: The implantation position of the electric field generating electrode is located at the periphery of the collecting electrode.

3. The electric field generating system according to claim 1 or 2, wherein: The collecting electrode comprises at least one of a ring electrode, a directional electrode, and an umbrella electrode; and / or The dielectric constant of the electric field generating electrode is greater than the dielectric constant of the collecting electrode; and / or The electric field generating electrode is an insulating electrode; and / or The outer tube of the electric field generating electrode is made of one or more of barium titanate, lead niobate, lithium niobate, polyvinylidene fluoride, polytetrafluoroethylene, and ceramic materials.

4. An electric field generating system according to any one of claims 1-3, wherein the electric field generating electrode comprises a first electrode, and when there is a cavity in the target tissue, the first electrode is used to be implanted into the cavity together with a charge storage material, and the charge storage material is in contact with both the first electrode and the target tissue.

5. The electric field generating system according to claim 4, wherein the electric field generating electrode further comprises a second electrode, and the second electrode is used to be implanted into the peripheral area of ​​the target tissue.

6. The electric field generating system according to any one of claims 1 to 3, wherein the electric field generating electrode comprises an outer tube, a conductor and a metal layer; The conductive wire and the metal layer are both located in the outer tube, and the metal layer is wound around the conductive wire to form a winding structure.

7. The electric field generating system according to claim 6, wherein the electric field generating electrode is divided into a plurality of electrode segments along its radial direction and / or axial direction, wherein each electrode segment is connected to a corresponding wire.

8. The electric field generating system according to claim 1, wherein: The electric field generating system includes multiple groups of electric field generating electrode pairs, each group of electric field generating electrode pairs includes two electric field generating electrodes implanted on both sides of the target tissue, and the multiple groups of electric field generating electrode pairs form an angle of 45° to 90° with each other.

9. The electric field generating system according to claim 1, wherein: A temperature sensor is integrated on the electric field generating electrode; and / or The electric field generating electrode and / or the collecting electrode are provided with a developing marker capable of being imaged in a medical image; and / or A cooling channel is provided inside the tube wall of the outer tube of the electric field generating electrode and / or inside the outer tube of the electric field generating electrode.

10. The electric field generating system according to claim 1, further comprising an electric field generator, wherein the electric field generator comprises a monitoring module, a control module and a suppression module; The monitoring module is used to receive the electrical signal collected by the collection electrode to monitor the growth of the target tissue; The control module is used to determine whether to generate a target electric field to the target tissue and / or adjust electric field parameters of the target electric field according to the growth condition; The suppression module is used to output a corresponding electric field signal to the target electric field generating electrode in response to receiving an electric field generating instruction for generating a target electric field and / or the electric field parameters.

11. The electric field generating system according to claim 10, further comprising a programmable control device disposed outside the body for controlling the collection electrode, the electric field generating electrode, and / or the electric field generator.

12. The electric field generating system according to claim 11, wherein the monitoring module and / or the program control device is further used for: constructing a conductivity distribution map of the target tissue and / or the surrounding tissue based on the collected electrical signals; The growth of the target tissue is monitored according to the conductivity distribution map.

13. The electric field generating system according to claim 11 or 12, wherein the control module and / or the program control device is further used to: determine the electric field strength of the target electric field generated to the target tissue according to the growth stage of the target tissue; wherein In response to the target tissue being in an early stage of inactive cell division, determining the electric field strength to be 1 V / cm to 2.25 V / cm; In response to the target tissue being in a progressive stage of active cell division, the electric field strength is determined to be greater than 2.25 V / cm.

14. The electric field generating system according to claim 11, further comprising an implantable ultrasonic sensor, which is used to be implanted into the peripheral area of ​​the target tissue; the ultrasonic sensor comprises an ultrasonic transmitting unit and an ultrasonic receiving unit, wherein The ultrasonic wave transmitting unit is used to transmit ultrasonic wave pulses to the target tissue and / or surrounding tissue; The ultrasonic receiving unit is used to receive ultrasonic pulses reflected by the target tissue and / or surrounding tissue, and convert the reflected ultrasonic pulses into ultrasonic electrical signals; The program-controlled device is also used to generate an ultrasonic image of the target tissue and / or surrounding tissue based on the ultrasonic electrical signal.

15. A method for using an electric field generating system, comprising using the electric field generating system according to any one of claims 1-14 to generate a target electric field to a target tissue.

16. The method of use according to claim 15, wherein before using the electric field generating system to generate a target electric field to a target tissue, the method of use further comprises: The target tissue is ablated using laser ablation technology, so that the electric field generating system is used to generate a target electric field for the ablated target tissue.

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